CN103272337A - Integrated external beam radiotherapy and mri system - Google Patents
Integrated external beam radiotherapy and mri system Download PDFInfo
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- CN103272337A CN103272337A CN2013100528569A CN201310052856A CN103272337A CN 103272337 A CN103272337 A CN 103272337A CN 2013100528569 A CN2013100528569 A CN 2013100528569A CN 201310052856 A CN201310052856 A CN 201310052856A CN 103272337 A CN103272337 A CN 103272337A
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- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
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- A61N5/1049—Monitoring, verifying, controlling systems and methods for verifying the position of the patient with respect to the radiation beam
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- A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
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- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1048—Monitoring, verifying, controlling systems and methods
- A61N5/1049—Monitoring, verifying, controlling systems and methods for verifying the position of the patient with respect to the radiation beam
- A61N2005/1055—Monitoring, verifying, controlling systems and methods for verifying the position of the patient with respect to the radiation beam using magnetic resonance imaging [MRI]
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- A61N5/10—X-ray therapy; Gamma-ray therapy; Particle-irradiation therapy
- A61N5/1077—Beam delivery systems
- A61N5/1081—Rotating beam systems with a specific mechanical construction, e.g. gantries
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Abstract
A radiation therapy system comprises a radiation source generating a beam of radiation and a magnetic resonance imaging apparatus. An interface acts between the radiation source and the MRI apparatus that permits irradiation to be performed simultaneously with imaging. The MRI apparatus and radiation source are coupled such that the system can be used in a rotation mode whereby the radiation source can irradiate a subject from basically any angle without reducing MRI image quality.
Description
The application is to be that on October 10th, 2006, application number are PCT/CA2006/001656 for the 200680046233.9(international application no applying date), denomination of invention divides an application for the application for a patent for invention of " integrated external beam radiotherapy and MRI system ".
Technical field
Present invention relates in general to radiotherapy, relate to a kind of integrated external beam radiotherapy beam treatment and NMR (Nuclear Magnetic Resonance)-imaging (MRI) system especially.
Technical background
Radiotherapy can be given to treat the hypertrophy _ tissue disorder including, but not limited to cancer, arteriovenous malformotion, skin injury etc.During radiotherapy, that the patient is known or suspect that the tissue comprise disease is exposed to radiation.Linear accelerator is generally used for shining the target volume that surrounds tissue to be treated during radiotherapy.As is known, linear accelerator uses microwave technology with the electronics in the accelerating waveguide, allows the electron collision heavy metal target then.As the result of collision, high-octane X ray is scattered from target.The X ray of part scattering is collected and is shaped to form by the beam alignment device output beam of the radiation consistent with the shape of target volume.Linear accelerator also comprises the door frame that rotates around the patient, to allow rendering to the target volume of expectation by rotating output beam that this door frame will radiate from any angle.
Before the patient is exposed to radiation, treatment plan usually _ propose so that the position of the tissue of determining exactly to treat and how best by this tissue of radiotherapy.Many imaging techniques in treatment plan, have been used, for example computed tomography (CT), NMR (Nuclear Magnetic Resonance)-imaging (MRI) and comprise single photon emission computed tomography (SPECT) and the radionuclide imaging of positron emission fault (PET).The image of the tissue that obtains is used to limit target volume so that consistent with target volume as far as possible with the actual tissue of irradiation by the output beam of radiation.Under many situations, the image that is used for the restriction target volume is obtained in single simulation.
For dose delivery, utilize the immobilized technology of tumor of for example passing through IMRT (Intensity Modulation Radiated Therapy (IMRT)) and image-guidance usually.The purpose of image-guidance is to guarantee that target tissue is arranged on the isocenter of linear accelerator when radiotherapy begins.Have in the tissue location of a large amount of histokinesises (for example pulmonary carcinoma radiotherapy) in expection, image guided therapy also constitutes the control of output beam of radiation to guarantee that irradiation time is restricted to the moment that is confined to the linear accelerator isocenter when tissue.
Unfortunately, if being used for the image of restriction target volume obtains in single simulation, then this method has basic difficulty, whether does not cause intended dose to be measured accurately being rendered to target and non-target tissue because know that the image-guidance of target position in subsequently treatment part copies.This is not know a priori whether the single simulation image represents location and the target volume structure of patient in subsequently the radiotherapy treatment fractions because be not.
In radiotherapy treatment fractions subsequently, correctly guide beam of radiation for the more accurate position information that relates to target tissue being provided and guaranteeing, considered linear accelerator and NMR imaging equipment integrated.
MRI is commonly known imaging technique.During MRI, be placed into the target that is generally human patients in the MRI machine and make it stand the uniform magnetic field that is produced by the polarized magnets that is contained in this MRI machine.Radio frequency (RF) pulse that is produced by the RF coil that is contained in the MRI machine according to specific positioning mode is used for the target tissue of scan patients.The MRI signal is radiated and is detected by the RF coil by the excited nucleus in the target tissue in the interval between continuous RF pulse.During the MRI signal detection, gradient magnetic is promptly changed to change the uniform magnetic field at regional area place, thereby allows the space orientation of the MRI signal that radiated by selecteed of target tissue.Detected MRI signal is digitized again and is processed, to utilize a kind of image of rebuilding the target tissue sheet in many known technologies.
A plurality of technical problems have been brought with linear accelerator and MRI device are integrated.For example, the operation of the magnetic field that is produced by the MRI device and linear accelerator is disturbed.In particular, the magnetic field that produces in the MRI device and the track of the electron beam in the linear accelerator disturb by magnetic force F=qvB, and can make electron beam deflection.For high-intensity magnetic field, deflection can enough force electron beam to enter accelerating waveguide greatly and stop electron beam arrival in the heavy metal target of accelerating waveguide output place.Even for the electron beam of part deflection, the angle that is incident on the heavy metal target of change can produce enough disturbances and cause its clinical can't acceptance bremsstrahlung X ray beam.
In addition, the magnetic field that is produced by the MRI device is disturbed in the existence of linear accelerator.For modern radiotherapy, need be with respect to patient's moving radiographic bundle, in order to make radiotherapy consistent with the shape of target volume.Being placed on the magnetic field line that wide variety of materials in the fringe magnetic field of MRI magnet will allow to extend to magnet homogeneous area (homogeneous region) changes.This itself is not problem, because this can be compensated; But if make this material move (if for example this material is linear accelerator, or around the shielding in cobalt source), then the disturbance of magnetic field in homogeneous area can cause unacceptable image fault.This problem all exists for linear accelerator and cobalt-based radiotherapy.
Another problem is that the receiving coil of the RF field that produced by linear accelerator and MRI device disturbs.This linear accelerator wherein goes out the RF that high-tension current to microwave generator (klystron or magnetron) produces microwave frequency by impulse modulation with the work of pulse power pattern, and this produces the suitable R F power that is transported to accelerating waveguide by the transmission waveguide pipe.This accelerating waveguide is the periodic structure that produces electric field, and this electric field is suitable for electronics is accelerated to megavolt level energy.The RF field that is produced by linear accelerator is comprised in these resonance, transmission and the accelerating structure, makes that not having appreciable power leakage to reach with the operation of MRI device disturbs.But this pulse power modulator produces the high-voltage pulse (being generally 50 to 100kV under 70 to 100A big electric current) that the persistent period is generally 4 microseconds.Rising and fall time are usually less than 1 microsecond.The frequency spectrum of pulse comprises the interior component of MHz scope of the noise signal that produces enough power, and the RF receiving coil of the noise signal of this enough power and MRI device obviously disturbs.The definite frequency of manipulator noise and power level depend on shape, the high-tension circuit of manipulator high-voltage pulse and hold the mechanical property of the structure of this high-tension circuit.
The U.S. Patent No. 6,366,798 of authorizing Green has disclosed the radiotherapy machine that comprises nuclear magnetic resonance imaging system.Radiotherapy machine by nuclear magnetic resonance imaging system to the zone and in abutting connection with this this zone for the treatment of curee in the regional volume imagery.The beam of imaging system and exiting coil component are arranged so that beam is not incident on the coil block.Exiting coil component comprises two winding segments that separate, for generation of main DC magnetic field.This section is positioned on this regional opposite side.The treatment chair that is used for the curee is engaged in the central opening of winding segments alignment.The coil block generation is edge and the main magnetic field lines of beam around the axis equidirectional extension of rotating usually.Do not discuss owing to the rotating beam generator is placed on the problem of the phase mutual interference that produces in the fixing nuclear magnetic resonance imaging system.
Authorize the British patent No.2 of Lagendijk, 393,373 have disclosed the linear accelerator integrated with the MRI device.The parts that provide and system prevent the magnetic field of MRI device and the operation interference of linear accelerator except other difficulty.
The U.S. Patent Application Publication No.2005/0197564 that authorizes Dempsey has disclosed device and the process that is used for carrying out the MR imaging during radiotherapy, by the Helmholtz coil groups MRI system that utilizes and the cobalt radioactive source is integrated.The required significant shielding in cobalt source during rotation can make the MR deterioration of image quality.
As realized, there are the needs for improved integrated linear accelerator and MRI device, its eliminating or alleviated the defective of identifying above at least one.Therefore, the treatment of conglomerate external radial bundle and NMR (Nuclear Magnetic Resonance)-imaging (MRI) device that the purpose of this invention is to provide a kind of novelty.
Summary of the invention
Therefore, provide a kind of radiotherapy system in one aspect, it comprises:
Radioactive source, this radioactive source can produce radiation beam;
NMR (Nuclear Magnetic Resonance)-imaging (MRI) device; With
Interface between radioactive source and the MRI device, this MRI device allows side by side to carry out radiation with imaging, wherein this MRI device and radioactive source are coupled and make this system to use with rotary mode, and radioactive source basically can be from any angular illumination curer under the situation that does not reduce MRI picture quality thus.
Radioactive source can be linear accelerator, comprise other particle accelerator that uses laser induced plasma, and it produces electromagnetic radiation (for example photon, X ray, coherent radiation), electronics, proton, carbon ion, other heavy ion, neutron or such as the radiation generating means of the subatomic particle of pi-meson, radioactive isotope power supply, radiation electromagnetic sound, heat, UV (ultraviolet) etc. or such as the relevant radioactive source of for example synchrotron.
In one embodiment, radioactive source can rotate under the situation that does not influence the MRI magnetic field homogeneity.Selectively, in another embodiment, it is fixing that radioactive source and MRI device keep, and rotation therapy is realized by the rotation by the curee.
In one embodiment, the pulsation of radioactive source can not take place in the RF of MRI device signal read-back simultaneously.In addition, can be lowered with the RF noise that the RF signal read-back of MRI device is disturbed.
According on the other hand, a kind of integrated radioactive source and NMR (Nuclear Magnetic Resonance)-imaging (MRI) system are provided, it comprises:
Radioactive source;
The MRI device;
Coupling device, this coupling device are coupled this radioactive source and MRI device; With
Disturb and reduce structure, this interference reduces structure and suppresses this radioactive source and the mutual interference of MRI device phase during operation.
In one embodiment, coupling device is coupled radioactive source and MRI device, so that radioactive source can not influence the magnetic field that is produced by the MRI device at radioactive source and/or MRI device between moving period.In one embodiment, this is by as one man moving radiographic source and MRI device are realized.Coupling device can be coupled the door frame of the door frame of radioactive source and MRI device or radioactive source and MRI device can be coupled to shared door frame.
Disturb the reduction structure can comprise the beam transfer, to keep the position by the electron beam that radioactive source was produced.In this case, the beam transfer comprises along the beam spot sensor of the accelerating waveguide setting of radioactive source and turns to coil arrangement.
In another embodiment, system also comprises two-dimension imaging apparatus.Imaging device and MR image are side by side caught an image in megavolt level axial image and the computed tomography image, are used for considering in treatment plan the generation of beam verification, aligning and the attenuation data of use.Selectively or combination with it, imaging device and MR image are side by side caught the SPECT image, are used for diagnostic message and the treatment plan improved.
According to another aspect, a kind of integrated radioactive source and NMR (Nuclear Magnetic Resonance)-imaging (MRI) system are provided, comprising:
Radioactive source;
The MRI device;
Coupling device, this coupling device are coupled this radioactive source and MRI device, wherein give the operation timing of radioactive source and MRI device, to suppress radioactive source and the mutual interference mutually of MRI device during operation.
In one embodiment, during reading, MRI device RF signal interrupts the radioactive source driving pulse.In addition, by being shaped, the radioactive source driving pulse reduces to read the RF noise of interference with MRI device RF signal by what radioactive source produced.
Integrated radioactive source and MRI system allow the operation effectively under the situation of radioactive source and MRI device non-interference during operation of radioactive source and MRI device.This allows to catch and use curee's image, to guarantee will correctly guiding to destination organization by the beam of radiation that radioactive source produces during radiotherapy treatment fractions.
Description of drawings
Referring now to accompanying drawing embodiment is described more fully, wherein:
Fig. 1 is integrated linear accelerator in the orientation and the partial schematic perspective view of MRI system;
Fig. 2 is the view in the transverse plane of the integrated linear accelerator of Fig. 1 in another orientation and MRI system;
Fig. 3 is the view in the integrated linear accelerator of Fig. 1 and the sagging plane of MRI system (saggital plane);
Fig. 4 forms the accelerating waveguide of a part of linear accelerator and the end-view of beam transfer;
Fig. 5 is the pulse train sketch map that the operation of the integrated linear accelerator of Fig. 1 to 3 and MRI system is shown;
Fig. 6 is the sketch map that the high-voltage pulse shape that is applied to linear accelerator is shown; With
Fig. 7 is the end-view of the alternate embodiments of integrated linear accelerator and MRI system.
The specific embodiment
Turn to Fig. 1 to 3 now, show integrated linear accelerator and MRI system, and generally with Reference numeral 10 labellings.As can be seen, integrated linear accelerator and MRI system 10 comprise linear accelerator (" linear accelerator ") 12 and MRI device 14.In fact linear accelerator in the application's scope refers to any radioactive source, such as for example particle accelerator or radioactive isotope power supply etc., it can produce and comprise for example radiation beam of X ray, gamma ray, electronics, proton, helium ion, carbon ion, other heavy ion or neutron.
In this specific example, MRI device 14 has the magnetic field intensity of 0.2T, and has the perforate pattern that comprises platform 16, and patient P can lie in this on 16 and be moved into and move out perforate for magnet/linear accelerator.The utmost point 18 and 20 of polarized magnets is arranged on the above and below of platform 16. Magnetic pole 18 and 20 is installed on the rotation door frame 22 that is supported by framework 24.
Except beam transfer 50, by placing around electron gun 33 and accelerating waveguide 36
(commercially available material with very high pcrmeability) barrier comes magnetic force ground shielding linear accelerator 12, to reduce the electron beam that produced by linear accelerator 12 as far as possible to the exposure in magnetic field.
As realized, utilize beam transfer 50 can dynamically compensate the changes of magnetic field that appears at linear accelerator 12 places, the electron beam that this changes of magnetic field influence produces therein.In addition, beam does not turn to and can cause
The changes of magnetic field that shielding is outer is disturbed with the operation of MRI device thereby suppress linear accelerator 12.
By linear accelerator 12 and MRI device 14 are fixed to identical door frame 22 MRI device and linear accelerator are as one man rotated, avoided the MRI distortion of field.As realized, if be independent of the rotation of MRI device or vice versa near the linear accelerator by the shielding of magnetic force ground in the magnetic field (make and have magnetic coupling between linear accelerator and MRI device) of MRI device, then motion will influence the changes of magnetic field in the MRI device imaging region.This will cause the inhomogeneities in MRI magnetic field, and this will cause unacceptable image fault.Be installed on the door frame 22 that mechanically is coupled to linear accelerator 12 by the magnetic pole 18 and 20 with MRI device 14, MRI device and linear accelerator rotate around the curee together, and the MRI magnetic field of combination also is like this.Therefore, guaranteed that MRI magnetic field is the function of gantry angle consistently, and image fault is removed.Image allows non-rotary image to be presented on the screen of MRI device by the reverse rotation of software.Shielding action may have to recursively finish in the magnetic field of linear accelerator 12 and the process of compensation MRI magnet, makes linear accelerator 12 conductively-closeds and magnet have till uniform at its isocenter until the setting of finding.But, in case obtain this initial setting, then remove the demand for the dynamic compensation of companion door frame rotation.
The magnetic pole 18 and 20 of guaranteeing linear accelerator 12 and MRI device 14 as one man rotates, and has avoided the very complicated dynamic compensation requirement in MRI magnetic field.Such compensation require MRI device complexity modeling and must be by many bucking coils of the feedback system dynamic driving of appropriate designs.
As previously known and describe, MRI device 14 is by reading the RF signal generator image that produces in the curee who is imaged.The RF pulse of transmission is tilted the magnetic moment of the proton of the tissue that is imaged.The frequency of proton precession depends on the magnetic field intensity that is set by gradient magnetic field coil.Phase information is set by applying second pulse, then by reading the RF signal and be embodied as picture based on known gradient fields reconstructed image from handling proton.This imaging sequence is finished with pulse operation, has certain repetition time between imaging sequence.
Transmit the power of the RF pulse that enters the patient apparently higher than the RF noise that is produced by linear accelerator 12, so the linear accelerator pulsation can not influence the RF pulse of transmitting.The SAR ultimate value of being set by FDA is 0.4W/kg.The power of launching from the pulsation of linear accelerator is in the scope of mW.But very little by handling the RF signal that proton produces in the curee, therefore any noise that is produced by linear accelerator 12 will disturb with the RF signal read-back process significantly, and may remove all imaging capabilities of MRI device 14.
In order to handle this problem, use timing sequence to guarantee that linear accelerator 12 does not produce pulse when MRI device 14 reads back the RF signal from the patient.Fig. 5 illustrates exemplary timing sequence.Two kinds of methods may be arranged.In one approach, changing MRI device 14 makes it produce its low-voltage signal will read the RF signal from the patient time of expression.This signal is connected and enters linear accelerator 12 and make the triggering signal that produces modulator pulses and electron gun pulse invalid.Therefore, this has produced MRI device 14 and can read back quiet RF cycle of RF signal.
Selectively, in second method, whole time cycle (magnitude of second) can be left for MRI imaging or linear accelerator pulsation.This method can be used in following system, and wherein linear accelerator disturbs with the MRI device when MRI device transmission RF, if perhaps pulse afterwards long enough die-away time of RF make that first method is infeasible.In this case, reduce the close rate of linear accelerator 12 and the imaging time of MRI device 14, therefore need the compromise between close rate and the image resolution ratio.
As will be appreciated, prevent that linear accelerator from hindering the ability that the MRI device reads the RF signal and allowing imaging and radiotherapy to pay execution simultaneously, and can be owing to linear accelerator produces interference to imaging sequence.
Also reduce the high-frequency components of the RF noise that is produced by linear accelerator 12, to reduce the interference between linear accelerator and the MRI device 14.The high pressure that is applied to the RF generator in the linear accelerator is the square wave with relative high-frequency components.The high drive pulse can be removed high-frequency components by suitably being shaped.By rising and the fall time of selecting electric capacity suitable on the PFN and inductance can change high-voltage pulse.This is shown in Figure 6.Although show specific drive pulse shape, those skilled in the art will recognize and to construct various pulse shapes.The restriction of only paired pulses shape is to need constant voltage regime during the time cycle that makes RF generator and electron gun impulsive synchronization, makes electronics and RF introduce accelerating waveguide 36 simultaneously.This change can cause producing the problem of the size of high-voltage pulse, because many systems are designed to use the square wave characteristic of high voltage pulse, so that the nominal voltage of high tension generator doubles.The possibility of result needs bigger high tension generator.
If desired, in order further to reduce the RF noise, can faraday cup be set around whole linear-accelerator structure, with the noise that suppresses to be produced by linear accelerator 12.This comprises pulse power modulator, transmission and accelerating waveguide and bremstrahlung heavy metal target.Copper shield can be incorporated in the heavy metal target, this can use in the design about the target of the filtration of X ray spectrum.
In above-mentioned example, MRI device 14 and linear accelerator 12 mechanically are coupled, so that magnetic pole and linear accelerator as one man rotate.Those skilled in the art will recognize other magnetic field that makes the MRI device and linear accelerator can be used with the coupling of avoiding magnetic disturbance takes place synchronously.
In addition, in the above-described embodiments, based on from the feedback of beam spot coil, utilize dynamic beam to turn to technology to realize residual magnetic field compensation magnet, that be present in linear accelerator 12 places from MRI device 14.Can use any forward method that utilizes feedback but those skilled in the art will recognize, correctly to locate the electron beam in the rectilinear transducer.
In addition, in the above-described embodiments, in the imaging process by some timing restriction being imposed on linear accelerator pulse train and the MRI device imaging pulse sequence, shielding to realize that by the modification of linear accelerator high-voltage pulse with by RF removing RF from linear accelerator 12 disturbs.The timing sequence that those skilled in the art will recognize other can be used for reducing RF to be disturbed.
Turn to Fig. 7 now, it shows another embodiment of integrated linear accelerator and MRI system.In this embodiment, the patient can receive treatment in the sitting posture structure.Linear accelerator 12 and MRI device 114 mechanically are coupled in order to flatly guide electron beam, and magnetic pole 118 and 120 vertically installed and make that magnetic field is level, but perpendicular to electron beam.Described two parts be fix and can not move.Be in curee in the sitting posture position by rotation and realize that variable angle electron penetrates input.
The benefit of this embodiment is to fit the following curee for the treatment of at the image-guidance counterdie, described curee can not cosily lie in lie on the back or prone position in the sufficiently long time to allow radiotherapy.This is particularly useful for some patients with lung cancer, but also useful to other curee.
Although MRI device 14 has been described as the magnetic field intensity with 0.2T, those skilled in the art will recognize magnetic field intensity that other can be arranged and other magnet design type, such as Helmholtz structure or opening " C " magnet configurations in pairs.In these cases, being in line with radioactive source such as two dimension (2D) imaging device of for example surface plate or other detector array is arranged on curee's opposite side, aims at so that megavolt level or core beam (core-beam) CT image, 2D projection beam verification or 2D to 3D to be provided.This structure has special application for simulation of radiotherapy treatment and provides the important megavolt level attenuation data for the treatment of plan calculating.In addition, Xiang Guan MRI provides for target and limits the synchronous images with fabulous soft tissue contrast.If radioactive source is the diagnosis X radial pipe, then can form CT and MR image simultaneously, use widely in diagnostic medicine, to give device.
In alternate embodiments, be suitable for diagnosing the 2D imaging device of nuclear medicine to be arranged in the opening between magnet the two poles of the earth, so that the SPECT imaging simultaneously with MRI to be provided.This structure utilizes the radioactive source in curee's body, rather than external radioactive source as mentioned above.As will be appreciated, this layout is provided at additional image-forming information useful in diagnostic medicine and the treatment plan.
Those skilled in the art will recognize because some detector system can be used in diagnosis CT and SPECT, so above-mentioned MRI-CT and MRI-SPECT system can make up to produce the MRI-CT-SPECT system.
Although above case description the use linear accelerator, those skilled in the art will recognize in fact and can use any radioactive source.For example, radioactive source can be to comprise another particle accelerator that uses laser induced plasma, and it produces electromagnetic radiation (for example photon, X ray, coherent radiation), electronics, proton, carbon ion, other heavy ion, neutron or the subatomic particle of pi-meson for example.Selectively, radiation source can be the radiation generating means of radioactive isotope power supply, radiation electromagnetic sound, heat, UV (ultraviolet) etc. or such as the isotope radioactive source of for example synchrotron.
Although at this embodiment has been described with reference to the drawings, but should be understood that the present invention is not limited to these definite embodiment, and under the situation that does not depart from scope and spirit of the present invention, can realize various other change and modification therein by those skilled in the art.All these change and modification is intended to be included in the scope of the present invention that claim limits.
Claims (21)
1. radiation therapy system comprises:
NMR (Nuclear Magnetic Resonance)-imaging equipment;
Radiation source, this radiation source can produce beam of radiation, this radiation source comprises power modulators, and this power modulators is shielded by the RF shielding, can read the RF noise that disturbs mutually with the RF signal of described NMR (Nuclear Magnetic Resonance)-imaging equipment to reduce by what described radiation source produced; With
Coupling device, this coupling device is used for being coupled described radiation source and described NMR (Nuclear Magnetic Resonance)-imaging equipment, make them as one man mobile, and described system can use with rotary mode,, under the situation that does not reduce NMR (Nuclear Magnetic Resonance)-imaging picture quality, side by side from any angle the curee is radiated basically with imaging with permission.
2. radiation therapy system as claimed in claim 1, wherein whole radiation source is shielded by the RF shielding.
3. radiation therapy system as claimed in claim 2, wherein said RF shielding comprises faraday cup.
4. radiation therapy system as claimed in claim 1, wherein said radiation source can rotate around the curee under the inhomogeneity situation that does not influence described NMR (Nuclear Magnetic Resonance)-imaging equipment magnetic field.
5. radiation therapy system as claimed in claim 1, wherein said radiation source and NMR (Nuclear Magnetic Resonance)-imaging equipment keep fixing, and the rotation by the curee realizes rotation therapy.
6. radiation therapy system as claimed in claim 1, wherein said radiation source and NMR (Nuclear Magnetic Resonance)-imaging equipment can as one man rotate.
7. radiation therapy system as claimed in claim 1, wherein said coupling device is coupled described radiation source and NMR (Nuclear Magnetic Resonance)-imaging equipment, so that described radiation source does not influence the magnetic field that is produced by described NMR (Nuclear Magnetic Resonance)-imaging equipment during described radiation source and NMR (Nuclear Magnetic Resonance)-imaging equipment moving.
8. radiation therapy system as claimed in claim 1, wherein said coupling device mechanically is coupled the door frame of described radiation source and the door frame of described NMR (Nuclear Magnetic Resonance)-imaging equipment.
9. radiation therapy system as claimed in claim 1, wherein said coupling device with described radiation source and NMR (Nuclear Magnetic Resonance)-imaging equipment coupling to the door frame that shares.
10. radiation therapy system as claimed in claim 1 comprises that also magnetic disturbance reduces structure, and this magnetic disturbance reduces structure and suppresses described radiation source and the mutual interference of NMR (Nuclear Magnetic Resonance)-imaging equipment phase during operation.
11. radiation therapy system as claimed in claim 10, wherein said interference reduce structure and comprise the beam turning facilities, to keep the position by the electron beam that described radiation source was produced.
12. radiation therapy system as claimed in claim 10, wherein said beam turning facilities comprises: along the beam spot sensor of the accelerating waveguide setting of described radiation source with turn to coil arrangement.
13. radiation therapy system as claimed in claim 10, wherein said interference reduce structure and comprise Alperm.
14. radiation therapy system as claimed in claim 1, the operation of wherein said radiation source and NMR (Nuclear Magnetic Resonance)-imaging equipment are timed to suppress described radiation source and the mutual interference mutually during operation of NMR (Nuclear Magnetic Resonance)-imaging equipment.
15. radiation therapy system as claimed in claim 14 is wherein interrupted the radiation source driving pulse during NMR (Nuclear Magnetic Resonance)-imaging device RF signal reads.
16. as each described radiation therapy system in the claim 1 to 15, also comprise two-dimension imaging apparatus.
17. radiation therapy system as claimed in claim 16, wherein said imaging device are caught one in megavolt level axial image and the Computerized chromatographic image.
18. radiation therapy system as claimed in claim 17, wherein megavolt level axial image or Computerized chromatographic image are caught simultaneously with nuclear magnetic resonance image, are used for calculating in treatment plan the generation of employed beam verification, registration and attenuation data.
19. radiation therapy system as claimed in claim 18, wherein Computerized chromatographic image and nuclear magnetic resonance image are caught simultaneously.
20. radiation therapy system as claimed in claim 16, wherein said imaging device is caught the SPECT image.
21. radiation therapy system as claimed in claim 20, wherein said SPECT image and nuclear magnetic resonance image are caught simultaneously, are used for improving diagnostic message and treatment plan.
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| JP2015096241A (en) | 2015-05-21 |
| CA2626538A1 (en) | 2007-04-26 |
| EP1948309A1 (en) | 2008-07-30 |
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| CN103272337B (en) | 2016-03-30 |
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| CA2626538C (en) | 2018-01-23 |
| JP5334582B2 (en) | 2013-11-06 |
| PL1948309T3 (en) | 2012-08-31 |
| EP1948309A4 (en) | 2009-11-11 |
| EP1948309B1 (en) | 2011-12-28 |
| HK1129616A1 (en) | 2009-12-04 |
| JP2013146610A (en) | 2013-08-01 |
| US20090149735A1 (en) | 2009-06-11 |
| JP2009511222A (en) | 2009-03-19 |
| ES2383983T3 (en) | 2012-06-28 |
| ATE538841T1 (en) | 2012-01-15 |
| US9468777B2 (en) | 2016-10-18 |
| CN101378805B (en) | 2013-03-27 |
| CN101378805A (en) | 2009-03-04 |
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